System for fourier domain optical coherence tomography

ABSTRACT

Optical coherence tomography (OCT) is an imaging method which can image with micrometer-scale resolution up to a few millimeters deep into, for example, living biological tissues and preserved tissue samples. An improved apparatus and image reconstruction algorithm for parallel Fourier Domain OCT which greatly eases requirements for interferometer stability and also allows for more efficient parallel image acquisition is provided. The apparatuses and algorithms reconstruct images from interfered, low-coherence, multiwave length signals having a π radian phase difference relative to one another. Other numbers of signals and other phase differences may be alternatively used, with some combinations resulting in higher resolution and image stability. The apparatus also eliminates a need for bulk optics to modulate a phase delay in a reference arm of the optical path. Images may be reconstructed using two spectrometers, where each is coupled to a detector array such as a photodiode array.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to U.S. Provisional Patent ApplicationSer. No. 60/473,457 filed May 28, 2003, which is incorporated herein byreference.

GOVERNMENT RIGHTS

This invention was made with United States Government support underFederal Grant No. BES 0134707 awarded by the National ScienceFoundation. The government has certain rights to this invention.

FIELD OF THE INVENTION

The invention relates to imaging systems and more particularly totomographic and interferometric imaging systems with high resolution.

BACKGROUND OF THE RELATED ART

Optical coherence tomography (OCT) is a method for noncontact opticalimaging taking advantage of sequential or scanned distance measurementsdeveloped primarily in the 1990's. In biological and biomedical imagingapplications, OCT allows for micrometer-scale imaging noninvasively intransparent and translucent biological tissues. The longitudinal rangingcapability of OCT is based on low-coherence interferometry, in whichlight from a broadband source is split between illuminating the sampleof interest and a reference path. The interference pattern of lightreflected or backscattered from the sample and light from the referencedelay contains information about the location and scattering amplitudeof the scatterers in the sample. In conventional (time-domain) OCT, thisinformation is extracted by scanning the reference path delay anddetecting the resulting interferogram pattern as a function of thatdelay.

The envelope of the interferogram pattern thus detected represents a mapof the reflectivity of the sample versus depth, called an “A-scan”, withdepth resolution given by the coherence length of the source. Inconventional OCT systems, multiple A-scans are acquired while the samplebeam is scanned laterally across the tissue surface, making a continuousseries of distance measurements and building up a two-dimensional map ofreflectivity versus depth and lateral extent called a “B-scan.” Thelateral resolution of the B-scan is given by the confocal resolvingpower of the sample arm optical system, which is usually given by thesize of the focused optical spot in the tissue.

Time-domain OCT systems have been designed to operate at moderate (˜1image/sec) and high speeds (up to video rate), and have been applied forimaging in biological applications such as imaging of embryonicdevelopment, as well as in medical diagnostic applications such asimaging the structures of the anterior and posterior segments of theeye, the skin, the gastrointestinal tract, and other tissues.Specialized probes, endoscopes, catheters, and biomicroscope attachmentshave been designed to allow for OCT imaging in these applications.

The time-domain approach in conventional OCT has been by far the mostsuccessful to date in supporting biological and medical applications,and all in-vivo human clinical trials of OCT to date have utilized thisapproach. However, the time-domain approach in OCT suffers from somelimitations. First, the requirement for mechanical scanning, such aswith bulk optics, of the reference delay in conventional OCT introducescomplexity, expense, and reduced reliability, especially those whichimage at high speed and acquire A-scans at kilohertz rates. Themechanical scanning reference delay line is typically the most complexoptical apparatus in high-speed conventional OCT systems, and can bequite bulky as well. Second, since conventional OCT images are built upserially using a single detector and collecting one pixel of imageinformation at a time, no advantage is taken of modern 1D and 2D arraydetection technologies which dominate other forms of optical imaging.

The serial collection or scanning approach of time-domain OCT is alsovery wasteful of sample arm light, in that an entire column of pixels isilluminated by that light while reflected light is only collected fromone pixel at a time. This wastefulness of sample arm light is costlybecause sources of broadband light suitable for use in OCT systems aretypically expensive and limited in their output power capability, andalso because optical damage to tissue structures often limits themaximum power which may be used in OCT imaging, particularly in theretina. Where there is a limit on the amount of light which may be usedto illuminate the sample, the wastefulness of sample arm lighttranslates directly into increased image acquisition time. Further, theserial scanning approach in conventional OCT requires that the sampleunder investigation remains stationary during the acquisition of eachA-scan, otherwise motion artifacts may appear in the image. Finally,primarily because of the requirement for a mechanical delay scan,conventional high-speed OCT systems are typically expensive, bulky, andrequire frequent optical alignment.

A potential solution to this need for a new approach has been variouslytermed spectral radar, Fourier-domain OCT (FDOCT), complex Fourier OCT,Optical Frequency-domain imaging, and swept-source OCT. In FDOCT, adifferent form of low-coherence interferometry is used in which thereference delay is fixed (except for potential wavelength-scale delaymodulation in some implementations), and information about the locationand amplitude of scatterers in the sample is derived from the opticalspectrum of the light returning from the sample and mixing with thereference. This spectral information is typically acquired by spectrallydispersing the detector arm light using a spectrometer and detecting itwith an array detector such as a charge-coupled device (CCD), or else byusing a single detector and sweeping the source frequency as a functionof time

The A-scan data collected using FDOCT can be shown to be related (seebelow) to the inverse Fourier transform of the spectral data thusacquired. Initial implementations of FDOCT suffered from image artifactsresulting from: 1) large direct-current (DC) signals appearing on thedetector array arising from non-interfering light returning from thereference delay and the sample, thus dwarfing the much smallerinterferometric signals; and 2) autocorrelation of light signals betweendifferent reflections within the sample. As a result, initial results ofFDOCT imaging were filled with artifacts and were not comparable toimages obtained with time-domain OCT.

Recently, newer implementations of FDOCT have appeared which takeadvantage of techniques well known from phase-shifting interferometry(PSI) to eliminate the sources of both of the artifacts mentioned above.Since both artifacts resulted from light appearing on the detector arraywhich does not arise from interference between sample and reference armlight, the recently introduced technique of complex FDOCT eliminatesthese artifacts by acquiring multiple spectra with different phaseshifts introduced into the reference delay path.

In a simple implementation of FDOCT, the reference delay consists of amirror mounted on a piezoelectric actuator (PZT). One spectrum isacquired at a given position of the mirror, and then another is acquiredwith a path-length delay of π/2 (resulting in a round-trip phase shiftof π) introduced into the reference arm by the PZT. It isstraightforward to show that this π phase shift reverses the sign of theinterferometric light components but has no effect on the DC componentsof the detector arm light, so subtracting the spectra obtained at 0 andπ phase shifts results in a spectrum free of DC artifacts. This spectrumcan be considered the real part of the complex Fourier transform of theA-scan. Thus, taking the inverse Fourier transform reconstructs theoriginal A-scan. However, since only the real part of the complexFourier spectrum is acquired, the A-scan data reconstructed isrestricted to be symmetric. Specifically, f(−z)=f*(z), and thus onlyA-scan data for positive displacements (i.e., z>0) can be reconstructed.

As a further refinement of this phase-shifting technique, an additionalspectrum may be acquired for a path-length delay of π/4 (correspondingto a round-trip phase shift of π/2). This spectrum (also optionallycorrected for DC components by division by one of the other spectra orby subtraction with a spectrum acquired with a path-length delay of3π/4) may be considered the imaginary part of the complex Fouriertransform of the A-scan. Thus, taking the inverse Fourier transform ofthe complete complex spectrum (resulting from all two, three, or fourphase measurements) allows for unambiguous reconstruction of all depthsin the sample limited only by spatial sampling considerations.Additional refinements to this approach may be applied which arecommonplace in phase-shifting interferometry, such as the use ofadditional phase delays for increased accuracy in measuring the complexspectrum.

Complex FDOCT thus addresses several of the needs for OCT systems withdecreased complexity and cost and increased reliability, having a mostlyfixed reference delay and utilizing an array detector. However, seriouslimitations to these prior art complex FDOCT implementations include: 1)a means is still required for displacing the reference delay bydistances on the scale of a wavelength; all prior systems perform thisfunction by using bulk optical devices outside of the reference armoptical fiber; and 2) the spectra obtained at different reference phasesare obtained sequentially, thus the sample and reference arms must bemaintained interferometrically motionless during the entire A-scanspectrum acquisition.

SUMMARY OF THE INVENTION

An object of the invention is to solve at least the above problemsand/or disadvantages and to provide at least the advantages describedhereinafter.

Another object of the invention is to provide an approach to OCT whicheliminates the need for a mechanically scanned reference delay and makesuse of array detection technologies to acquire signals from allilluminated axial pixels of an A-scan simultaneously.

Another object of the invention is to enable the construction of OCTsystems which are inexpensive, compact, and are mechanically stable suchthat they rarely require optical realignment.

Another object of the invention is to provide an improvement to FDOCTwhich does not require any means for modulation of the reference armpath length, or may accomplish such modulation within the existingreference arm optical fiber.

Another object of the invention is to provide an FDOCT system whichobtains the multiple phase delays required for elimination of imageartifacts and/or removal of constraints on A-scan asymmetrysimultaneously, thus relaxing constraints on sample and reference motionduring A-scan acquisition.

To achieve the aforementioned objects, an improved system for FDOCT isprovided which implements readout of multiple reference phases in two ormore detector channels simultaneously.

To further achieve the aforementioned objects, an improved system forFDOCT is provided which eliminates the need for a mechanically scannedreference delay and makes use of array detection technologies orwavenumber swept sources to acquire signals from all illuminated axialpixels of an A-scan simultaneously.

To further achieve the aforementioned objects, a method is providedwhich takes advantage of inherent π phase differences between differentports of interferometers, and which also utilizes orthogonalpolarization channels within the reference delay to encode arbitraryphase delays is provided.

To further achieve the aforementioned objects, a system is provided thatutilizes photodiode arrays for optimal S/N ratio in FDOCT.

To further achieve the aforementioned objects, a system is provided thatutilizes silicon-based photodiode arrays for FDOCT in the 830 nm OCTwindow and InGaAs arrays for FDOCT in the 1310 nm and 1550 nm spectralregions. Further advantages of the use of dual-stripe andtwo-dimensional CCD and photodiode arrays are also disclosed.

Additional advantages, objects, and features of the invention will beset forth in part in the description which follows and in part willbecome apparent to those having ordinary skill in the art uponexamination of the following or may be learned from practice of theinvention. The objects and advantages of the invention may be realizedand attained as particularly pointed out in the appended claims.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention will be described in detail with reference to thefollowing drawings in which like reference numerals refer to likeelements wherein:

FIG. 1A is a schematic illustration of a first embodiment of a FDOCTsystem, in accordance with the present invention;

FIG. 1B is a schematic illustration of a second embodiment of a FDOCTsystem, similar to the embodiment of FIG. 1, that utilizes a supportfrequency source, in accordance with the present invention;

FIG. 2 is a schematic illustration of a third embodiment of a FDOCT,system in accordance with the present invention;

FIG. 3 is a schematic illustration of a fourth embodiment of a FDOCTsystem, in accordance with the present invention;

FIG. 4 is a schematic illustration of a fifth embodiment of a FDOCTsystem, in accordance with the present invention;

FIG. 5 is a schematic illustration of a sixth embodiment of a FDOCTsystem, in accordance with the present invention;

FIG. 6 is a schematic illustration of a seventh embodiment of a FDOCTsystem, in accordance with the present invention;

FIG. 7 is a generalized schematic illustration of a eighth embodiment ofa FDOCT system, in accordance with the present invention; and

FIG. 8 is a schematic illustration of an imaging spectrometer, inaccordance with the present invention.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS

Referring to FIG. 1A, a first FDOCT 10 in accordance with one embodimentof the present invention, is shown. The FDOCT 10 of FIG. 1A includes anoptical circulator 34 with three ports 34 a, 34 b and 34 c, and a firstfiber coupler 36 having four Michelson interferometer ports 37 a, 37 b,37 c and 37 d. The optical circulator 34 and the first fiber coupler 36together make up an optical manipulator 1. The first fiber coupler 36 iscoupled to a first polarization controller 42 by a single mode (SM)optical fiber 41. The first polarization controller 42 is coupled to afirst phase modulator 44 by a SM optical fiber 48. The first phasemodulator 44 is coupled to a SM optical fiber 51 which terminates in areflector 46. Together the first polarization controller 42, first phasemodulator 44 and reflector 46, plus SM optical fibers 48 and 46, form areference arm.

A second polarization controller 54 is coupled by a SM optical fiber 52to the first fiber coupler 36. The second polarization controller 54 isoptically coupled to a first lens 56 by a SM optical fiber 65. The firstlens 56 is configured to capture a signal exiting the SM optical fiber65, and direct the signal to scanning optics 58, preferably a moveablemirror. The scanning optics 58, together with second lens 61, directsthe signal onto a sample 62 and receive a reflected signal therefrom.The second polarization controller 54, first lens 56, scanning optics58, and second lens 60, a SM optical fiber 52 and SM optical fiber 65form a sample arm. Applicant notes that the terms “signal,” “beam,” and“light” are used synonymously to include all forms of electromagneticradiation suitable for use in imaging systems.

Also connected by a SM optical fiber 64 to the first fiber coupler 36 isa first detector 66 having a first spectrometer 66 a and first arraydetector 66 b. A second detector 71 is coupled to the optical circulator34 by a SM optical fiber 68. The optical circulator 34 may additionallybe configured to receive a signal from a source 72 through a SM opticalfiber 74. The first and second detectors, 66 and 71, and SM opticalfibers 64 and 68 together form a detector portion of the FDOCT 10.

The FDOCT system 10 is preferably implemented using a SM fiber Michelsoninterferometer illuminated by a broadband short-coherence length lightsource 72. Light from the source 72 may be evenly split between sampleand reference arms by the first fiber coupler 36. The sample arm canoptionally include a second polarization controller 54 for controllingthe polarization state of the optical signal and scanning mirror 58 andlens 61 for scanning and focusing the sample arm signal onto the sample62.

The reference arm may have a fixed path length, preferably obtained byplacing a reflector 46 on the tip of the reference arm fiber 51 (thuseliminating bulk optics entirely in the reference arm and thesubstantial losses incurred in coupling out of and back into the SMfiber 51).

The reference arm may also optionally include a first polarizationcontroller 42 for matching the polarization state in the reference armto that in the sample arm, and may also optionally include a first phasemodulator 44 which is capable of selectively causing wavelength-scalevariations in the reference delay under user control. The first phasemodulator 44 can be placed in the sample arm in this and all subsequentimplementations without any loss of functionality. Light from the thirdport 34 c of the first circulator 34 and light from the third Michelsoninterferometer port 37 c of the fiber coupler 36, having 180° phasedifference between them may be coupled into a pair of detectors, 71 and66 respectively. Detectors 66 and 71 each preferably includespectrometers 66 a and 71 a, and array detector, 66 b and 71 b,respectively. This configuration is designed to place copies of thephase-shifted optical spectrum onto a matched pair of array detectors.

The FDOCT 10 of FIG. 1A acquires a pair of FDOCT spectra, with .pi.radians phase difference between them, on a pair of array detectors toeliminate most motion artifacts associated with conventional phase-shiftinterferometry. Spectrometers 66 a and 71 a, and array detectors 66 band 71 b are preferably matched as closely as possible in their opticaland electronic characteristics. This can be accomplished by usingspectrometers and detector arrays of matching design.

In operation, the FDCOT 10 acquires spectra having a relative phasedelay of 180° between them from interferometer ports 37 c and 3 of theinterferometer, and differences the spectra in order to eliminate sampleand reference arm DC and sample arm autocorrelation terms. The resultingdifference spectrum is inverse Fourier transformed to acquire aone-sided A-scan. Care must be taken to assure that the length of thereference arm is adjusted so that no reflections are observed for z<0.

In an alternative mode of operation, the FDOCT 10 acquires a 180°relative phase delay between them and differences them in order toeliminate most sample and reference arm DC and sample armautocorrelation terms, as designated above. The first phase modulator 44in the reference arm is then adjusted for 90° of additional referencedelay. Simultaneous spectra having 90° and 270° phase delay between themare then acquired and differenced in order to eliminate most sample andreference arm DC and sample arm autocorrelation terms. The first andsecond difference spectra may then be taken as the real and imaginaryparts, respectively, of the complex Fourier transform of the two-sidedA-scan. An inverse Fourier transform may be performed on the complexdata to obtain the A-scan free of symmetry considerations. Additionalphase delays of the first phase modulator 44 may also be selected, andorthogonal pairs of spectra obtained, according to establishedalgorithms for phase-shift interferometry.

FIG. 1B shows a second FDOCT 15, in accordance with a second embodimentof the present invention. The FDOCT 15 fifteen of FIG. 1B is similar tothe FDOCT system 10 of FIG. 1A, except that a swept-frequency source 720is used in place of the broadband short-coherence length light source 72of FIG. 1A. In addition, single-channel detectors 800A and 800B are usedin place of the spectrometer/array detector combinations of FIG. 1A.

The swept-frequency source 720 is preferably a narrowband light sourcewhose frequency can be swept as a function of time. In the embodiment ofFIG. 1B, the spectrum of the interferometer output(s) is obtained bymonitoring the output of the detectors 800A, 800B as a function of timewhile the frequency of the swept-frequency source 720 is swept.

The additional embodiments discussed below will be shown with abroadband light source, and with spectrometer/array detector(s) thataree used to resolve the spectrum of the interferometer output. However,it should be appreciated that all of the embodiments described below canalso be implemented in a swept-source configuration, such as theconfiguration shown in FIG. 1B, by replacing the broadband source with aswept-frequency narrowband source, and by replacing each detector with asingle-channel time-resolved detector. When Fourier Domain OCT isperformed using a swept-source implementation, then all of the sameadvantages conferred by obtaining multiple simultaneous phasedifferences, either from multiple output ports of the variousinterferometer topologies, from polarization encoding of phase in theinterferometer arms, or a combination of both approaches, will apply.

FIG. 2 shows a second FDOCT embodiment 20, in accordance with thepresent invention. Similar to the FDOCT embodiment 10 shown in FIG. 1A,the FDOCT embodiment 20 of FIG. 2 has a fiber coupler 36 connected to afirst polarization controller 42 by a SM optical fiber 41. The firstpolarization coupler 42 is connected to a phase modulator 44 by a SMoptical fiber 48. The phase modulator 44 has a fiber 51 extendingtherefrom terminating in a reflector 46. Additionally, the first fibercoupler 36 is connected to a second polarization controller 54 by a SMoptical fiber 52. The second polarization controller 54 is opticallycoupled to a first lens 56 by a SM optical fiber 64. The first lens 56directs an optical output signal from fiber 64 to scanning optics 58.Scanning optics 58 and lens 61 direct the optical signal to sample 62.Reflected optical signals from the sample 62 are coupled back into fiber64 via lens 61 scanning optics 58 and lens 56.

The first fiber coupler 36 is also connected to a first detector 66 by aSM optical fiber 64. In a variation from the first FDOCT embodiment 10,the first fiber coupler 36 is connected to a second fiber coupler 76through a SM optical fiber 38. The second fiber coupler 76 is connectedto a second detector 71 through a SM optical fiber 68, and includes a 0°port 75 and a 180° port 77. The second fiber coupler 76 also includes aSM optical fiber stub 78 connected to the 180° port 77. A low coherencesource 72 may also be connected to the second fiber coupler 76 through aSM optical fiber 74.

The FDOCT embodiment 20 of FIG. 2 is similar in many respects to theFDOCT embodiment 10 of FIG. 1A, except that a second fiber coupler 76 isused in the source arm to provide one of the orthogonal phasecomponents, in place of the first circulator 34 of FIG. 1A. Use of asecond fiber coupler 76 may be preferable for decreasing system cost orif circulators are not available to meet the specified wavelength orbandwidth requirements. The penalty for use of the second fiber coupler76 in place of a circulator will result in a higher insertion loss (3 dBfor a fiber coupler versus -0.7 dB for a circulator) in the forwarddirection, plus a 3 dB loss in the reverse direction of the 0.degree.port 75, which will need to be matched by an equal amount of attenuationof the 180.degree. port 64 in order to match DC levels on the detectors66 and 71.

Thus, the FDOCT embodiment 20 may experience a total loss of sourcelight of approximately 6 dB loss (not counting circulator insertionlosses) as compared to the FDOCT embodiment 10. As in the FDOCTembodiment 10 of FIG. 1A, the separate spectrometers 66 a and 71 a, andarray detectors 66 b and 71 b of the first and second detectors 66 and71 could be replaced by an imaging spectrometer and a dual-row orthree-color detector array. Also, any of the three modes of operationdiscussed in connection with the FDOCT embodiment 10 of FIG. 1A may alsobe used in the FDOCT of FIG. 2.

FIG. 3 illustrates a third FDOCT embodiment 30, in accordance with thepresent invention. Similar to the FDOCT embodiments 10 and 20 discussedabove, the FDOCT embodiment 30 includes a fiber coupler 36 coupled to asecond polarization controller 54 through a SM optical fiber 52. Thefirst fiber coupler 36 includes interferometer ports 37 a, 37 b, 37 cand 37 d. The second polarization controller 54 is optically coupled toa first lens 56 through a SM optical fiber 56. The first lens 56 directsand receives signals to and from a sample 62 through scanning optics 58and second lens 61.

Also attached to the first fiber coupler 36 is a reference arm includinga second phase modulator 84 connected to the first fiber coupler 36 witha SM optical fiber 82. The second phase modulator 84 is connected to athird polarization controller 88 with a SM optical fiber 86. The thirdpolarization controller 88 is connected to a third fiber coupler 94through a SM optical fiber 92. The third fiber coupler 94 is alsoconnected to the first fiber coupler 36 with a SM optical fiber 96. Thethird fiber coupler 94 is connected to a first detector 66 and a seconddetector 71 through SM optical fibers 64 and 68, respectively. The FDOCTembodiment 20 of FIG. 2 may also include a source 72 coupled to thefirst fiber coupler 36 through a SM optical fiber 75.

FIG. 3 illustrates a FDOCT embodiment 30, in accordance with the presentinvention, which takes advantage of the intrinsic phase differencebetween interferometer ports 37 a and 37 b of the first fiber coupler36, but has a transmissive reference delay rather than a reflective one.Other aspects of the FDOCT embodiment 30 are similar to the previouslydiscussed FDOCT embodiments 10 and 20. The FDOCT embodiment 30 of FIG. 3may experience a loss of 3 dB of the sample arm reflected light (whichis returned into the source). However, this 3 dB loss is less than thecorresponding configurations in other FDOCT embodiments, and isapproximately the same loss experienced by time-domain OCT in aconventional Michelson interferometer. Thus, the FDOCT embodiment 30 ofFIG. 3 is the preferred implementation when a circulator is unavailableor undesirable. As in the previously discussed FDOCT embodiments 10 and20, optimally the first and second spectrometers 66 a and 71 a and firstand second array detectors 66 b and 71 b could be replaced by an imagingspectrometer and a dual-row or three-color detector array. Also, any ofthe three modes of operation discussed above in connection with FDOCTembodiments 10 and 20, may also be used.

FIG. 4 illustrates a fourth FDOCT embodiment 40, in accordance with thepresent invention. The FDOCT embodiment 40 includes a first fibercoupler 36 which is coupled to a first polarization controller 42 by aSM optical fiber 41. The first fiber coupler 36 has four interferometerports 37 a, 37 b, 37 c, and 37 d. One interferometer port 37 a iscoupled to a first polarization controller 42 by a SM fiber 41, and thesecond interferometer port 37 b is coupled to a second polarizationcontroller 54 by a SM fiber 52. The first polarization controller 42 iscoupled to a first phase modulator 44 by a SM optical fiber 48. Thesecond polarization controller 54 is coupled to the first fiber coupler36 by a SM optical fiber 52, and to a second circulator 102 by a SMoptical fiber 64. The second circulator 102 has a SM optical fiber 110optically coupled to a first lens 56, which directs and receives asignal to and from a sample 62 through scanning optics 58 and secondlens 61. The second circulator 102 is also coupled to a fourth fibercoupler 98 through a SM optical fiber 104. The first phase modulator 44is also coupled to the fourth fiber coupler 98 by a SM fiber 50.

The fourth fiber coupler 98 is coupled to first and second detector 66and 71 through SM optical fibers 64 and 68, respectively. The FDOCTembodiment 40 may also include a first source 72 coupled to the firstfiber coupler 36 through a SM optical fiber 74 and a second source 106coupled to the fiber coupler 36 through a SM optical fiber 108.

The FDOCT embodiment 40 of FIG. 4 takes advantage of the intrinsic phasedifference between interferometer ports 37 a and 37 b, and also has atransmissive delay. However, the FDOCT embodiment 40 uses a secondcirculator 102 to direct light onto the sample 62. The FDOCT embodiment40 also places the second circulator 102 within one of the arms of theinterferometer, where chromatic and polarization mode dispersion effectswithin the second circulator 102 may be problematic.

However, the embodiment 40 makes highly efficient use of source light(except for insertion losses in the circulator 102 itself), and alsoallows for the introduction of a second source 106. This may bepreferable in order to increase the power of low-coherence light on thesample 62 from available light sources 72 and 106, and also may be usedto increase the bandwidth of illumination by using sources withdisplaced center wavelengths. As in the previously discussed FDOCTembodiments 10, 20 and 30, the separate spectrometers 66 a and 71 a andarray detectors 66 b and 71 b could be replaced by an imagingspectrometer and a dual-row or three-color detector array. Also, any ofthe three modes of operation discussed above in connection with thepreviously discussed FDOCT embodiments 10, 20 and 30 may be used in theFDOCT embodiment 40 of FIG. 4.

All the FDOCT embodiments discussed above may take advantage of theintrinsic π phase delay which is found between output ports of Michelsonand Mach-Zehnder interferometers. As described above, this phase delaymay be used to simultaneously obtain pairs of spectra which may bedifferenced to remove non-interferometric noise from the spectral data.However, it also may be desirable to obtain pairs of spectra with π/2phase delay simultaneously, to allow for both removal ofnon-interferometric noise and also for unambiguous calculation of samplereflectivity without symmetry artifacts. The embodiments described belowtake advantage of polarization to encode arbitrary phase delays intospectra which may be measured simultaneously.

FIG. 5 illustrates a fifth FDOCT embodiment 50, in accordance with thepresent invention. The FDOCT embodiment 50 includes a non-polarizingbeam splitter 114 optically coupled to a λ/n waveplate 116 and a fixedreference mirror 118. The non-polarizing beam splitter 114 is alsooptically coupled to a sample 62 through scanning optics 58 and secondlens 61. The non-polarizing beam splitter 114 is additionally opticallycoupled to a polarizing beam splitter 120. Polarizing beam splitter 120is optically coupled to a first detector 66 through lens 122, and asecond detector 121 through lens 124. The FDOCT embodiment 50 may alsoinclude a source 72 optically coupled to the non-polarizing beamsplitter 114 through a polarizer 112.

The FDOCT embodiment 50 is similar to a bulk-optic Michelsoninterferometer which may encode a 90° phase shift into two polarizationchannels, which are separated outside of the interferometer by thepolarizing beam splitter 120. The two polarization channels may bedirected into a matched pair of spectrometers 66 a and 71 a and arraydetectors, 66 b and 71 b. Light emitted from the preferablylow-coherence source 72 may be linearly polarized at 45° from thevertical by a polarizer 112 placed in the source arm. The non-polarizingbeamsplitter 114 splits this light evenly between sample and referencearms. A λ/n waveplate 116 (for n=2, 4, 8, etc.) may be placed in thereference arm, with its fast axis oriented vertically (i.e., at 0° tothe vertical).

Thus, the horizontal component of the light in the reference arm mayexperience a phase delay of 4π/n radians with respect to the verticalcomponent after double-passing the λ/n waveplate 116. These twocomponents may be separated by the polarizing beamsplitter 120 in thedetector arm, which sends the phase-delayed components of the referencearm light, along with an equal division of the light reflected from thesample 62, into a matched pair of spectrometers 66 a and 71 a, and arraydetectors, 66 b and 71 b.

For example, for n=8, i.e. an eighth-wave plate in the reference arm,there will be a λ/4 or 90° phase difference between the spectra obtainedfrom the reference and sample arms, which is sufficient for unambiguousreconstruction of the sample reflectivity from the complex spectrum thusobtained. For other values of n, i.e., n=4 (quarter-wave plate), n=2(half-wave plate), other phase delays between the collected spectra mayalso be obtained as needed for various phase-shift interferometryreconstruction algorithms. Although only 2 phase delays may be encodedinto polarization, the polarization-based approach of the FDOCTembodiment 50 may be combined with the intrinsic interferometer portphase difference methods of the other FDOCT embodiments discussed aboveto obtain at least 4 simultaneous spectra with different phase delays.

As another example, the addition of a circulator into the source arm ofthe FDOCT embodiment 50, which may direct light into another polarizingbeamsplitter and two more spectrometers, would allow for thesimultaneous acquisition of spectra having 0°, 90°, 180°, and 270° phasedifferences. It will be clear to one of ordinary skill in the art thatnumerous other implementations of the inventive concept of polarizationencoding of phase may be used as extensions of the FDOCT embodiment 50,such as the rotation of all polarization-sensitive elements in theembodiment 50 by a fixed angle, or numerous alternative placements ofthe polarization-sensitive elements (including placing of the λ/n plate116 in the sample arm instead of the reference arm), while still fallingwithin the scope of the present invention.

Modes of operation of the FDOCT embodiment 50 of FIG. 5 includesacquiring simultaneous spectra having 0° and 180° phase delay by use ofa λ/4 waveplate in the reference arm. The spectra may be differenced inorder to eliminate sample and reference arm DC and sample armautocorrelation terms. The resulting difference spectrum may be inverseFourier transformed to acquire a one-sided A-scan. The length of thereference arm is preferably adjusted so that no reflections are observedfor z<0.

Another mode of operation for use with the FDOCT embodiment 50 of FIG. 5includes acquiring simultaneous spectra having 0° and 90° phase delaybetween them and differencing them in order to eliminate sample andreference arm DC and sample arm autocorrelation terms. These spectra maybe taken as the real and imaginary parts, respectively, of the complexFourier transform of the two-sided A-scan. The inverse Fourier transformmay then be performed on the complex data to obtain the A-scan free ofsymmetry considerations.

Another mode of operation for use with the FDOCT embodiment 50 of FIG. 5includes acquiring simultaneous spectra having 0°, 90°, 180°, and 270°phase difference between them, by use of a combination of polarizationencoding of phase and intrinsic phase delay between interferometerports, as described above. Pairs of spectra having 180° phase delaybetween them may be differenced in order to eliminate sample andreference arm DC and sample arm autocorrelation terms. The differencedpairs of spectra may then be taken as the real and imaginary parts,respectively, of the complex Fourier transform of the two-sided A-scan.The inverse Fourier transform may be performed on the complex data toobtain the A-scan free of symmetry considerations.

FIG. 6 illustrates a sixth FDOCT embodiment 60, in accordance with thepresent invention. The FDOCT embodiment 60 includes a first fibercoupler 36 coupled to a first polarization controller 42 through a SMoptical fiber 41. The first polarization controller 42 is coupled to aSM optical fiber 51, which terminates in a reflector 46. The first fibercoupler 36 is also coupled to a second polarization controller 54through a SM optical fiber 52. The second polarization controller 54 isoptically coupled to a first lens 56 through a SM optical fiber 64. Thefirst lens 56 is optically coupled to a sample 62 through a scanningoptics 58 and second lens 61. The first fiber coupler 36 is also coupledto a third lens 126 through a coupler 64. The third lens 126 isoptically coupled to a polarizing beam splitter 120. The polarizing beamsplitter 120 is optically coupled to a lens 122 and a first detector 66.The polarizing beam splitter 120 is also optically coupled to a lens 124and a second detector 71.

It is preferable to have the capability for arbitrary simultaneous dualphase delays between acquired spectra in a fiber interferometer, sincemost practical OCT systems to date make use of the flexibility of fiberoptic systems for medical and biological applications. The FDOCTembodiment 60 illustrates one possible implementation of a fiber-opticinterferometer for imaging, which uses polarization for phase encoding.In this embodiment, the light source 72 is either polarized or apolarization element 112 (such as a fiber polarizer) is used in thesource arm. Preferably, the interferometer is constructed frompolarization-maintaining fiber (PMF), although previous work inpolarization-sensitive OCT has shown that non-PMF fiber is also capableof maintaining phase relationships between orthogonal polarizationstates propagating through the fiber. In the FDOCT embodiment 60 of FIG.6, a fiber polarization controller 42 in the reference arm may be usedto simulate the λ/n waveplate 116 in the FDOCT embodiment 60, and thesecond polarization controller 54 in the sample arm may be used tocorrect for stress-induced birefringence in the sample arm fiberassembly.

Although the FDOCT embodiment 60 is just one example of polarizationphase encoding in a fiber interferometer, any of the fiberinterferometers shown in the FDOCT embodiments described above could bealtered to use polarization phase encoding by the addition of a PBS andmatched pair of spectrometers to each output port 37 a and 37 b.Modifications of the FDOCT embodiments described above in this way wouldresult in the simultaneous collection of spectra with 4 phase delays(pairs of which are separated by 180°), since each of thoseimplementations have dual interferometer outputs.

FIG. 7 shows a generalized embodiment 100 of a FDOCT system, inaccordance with the present invention. The FDOCT 100 includes a signalmanipulator 12. The signal manipulator 12 is coupled to a referenceportion 14 by a coupler 20, and a sample portion 16 by a coupler 22. Thesignal manipulator 12 is also coupled to a detector 18 by a coupler 24.The signal manipulator 12 may also be coupled to a source 26 by acoupler 28. The sample portion 16 is coupled 31 to a sample 32.

Examples of signal manipulator 12 of FIG. 7 can include, but are notlimited to, the combination of the first optical circulator 34 and thefirst fiber coupler 36 of FIG. 1, the second fiber coupler 76 and firstfiber coupler 36 of FIG. 2, and the first fiber coupler 36 of FIGS. 3and 4. Additionally, the signal manipulator 12 of FIG. 7 may alsocorrespond to the polarizer 110 and nonpolarizing beam splitter 114 ofFIG. 5, and the polarizing element 112 with the fiber coupler 36 of FIG.6.

The reference portion 14 of FIG. 7 may include, but is not limited to,the combined first polarization controller 42, first phase modulator 44,and reflector 46 of FIGS. 1 and 2. The reference portion 14 of FIG. 7may also include, but is not limited to, the second phase modulator 84and third polarization controller 88 of FIG. 3, and the firstpolarization controller 42 and first phase modulator 44 of FIG. 4. Thereference portion 14 of FIG. 7 may also include, but is not limited to,the combination of the λ/n plate 116 and reference mirror 118 of FIG. 5,and the first polarization controller 42 and reflector 46 of FIG. 6.

The sample portion 16 of FIG. 7 may include, but is not limited to, thesecond polarization controller 54, first lens 56, scanning optics 58 andsecond lens 61 of FIGS. 1, 2, 3 and 6. The sample portion of FIG. 7 mayalso include, but is not limited to, the combination of the secondpolarization controller 54, second optical circulator 102, first lens56, scanning optics 58 and second lens 61 of FIG. 4, and the scanningoptics 58 and second lens 61 of FIG. 5.

The detector 18 of FIG. 7 may include, but is not limited to, the firstdetector 66 and second detector 71 of FIGS. 1 and 2. The detector 18 ofFIG. 7 may also include, but is not limited to, the combination of thefirst and second detectors 66 and 71, and the third fiber coupler 94 ofFIG. 3, and the first and second detectors 66 and 71, and the fourthfiber coupler 98 of FIG. 4. Finally, the detector 18 of FIG. 7 mayinclude, but is not limited to, the first and second detectors 66 and71, the lens 124 and the lens 122, and the polarization beam splitter120 of FIGS. 5 and 6, as well as the third lens 126 of FIG. 6.

It should also be noted that the source 26 shown in FIG. 7 may include,but is not limited to, the first source 72 of FIGS. 1, 2, 3, 5 and 6.The source 26 of FIG. 7 may also include, but is not limited to, thefirst source 72 and second source 106 of FIG. 4.

Referring to FIG. 8, a detector 66 with imaging capabilities suitablefor use with FDOCT embodiments 10, 20, 30, 40, 50, 60 and 100 is shown.The detector 66 has dual input fibers 128 and 129 coupled to an inputslit 136 of the detector 66. The detector 66 also includes an outputarea 130. The output area includes a first array 132 and a second array134 which may receive two spectra, 138 and 140.

In operation, the detector 66 receives two multi-frequency signalscarried in the dual input fibers 128 and 129, at the input slit 136. Theinput signals preferably have a phase difference between them, and thephase difference is preferably 90 degrees. Each input signal is thendispersed according to frequency and the resulting spectra 138 and 140,are directed onto the arrays 132 and 134. The arrays 132 and 134, maythen measure power as a function of frequency for each spectrum 138 and140.

The previously described FDOCT embodiments 10, 20, 30, 40, 50, 60 and100 all preferably take advantage of the detection of multiplesimultaneous optical spectra in the detector arm of the interferometer,corresponding to multiple phase-delayed components of a complex FDOCTsignal. FIGS. 1-7 illustrate simple cases of dual-channel detection ofspectra separated by orthogonal (90°) or opposite (180°) phase obtainedthrough the use of intrinsic phase delays associate with interferometerports, or through polarization multiplexing. A combination of intrinsicand polarization-derived phase delays could also be used to obtain atleast four simultaneous phase delays, which would preferably be detectedin an equal number of spectral channels. Although four or moresimultaneous phase delays may be desirable to accommodate somephase-shift interferometry reconstruction algorithms, collection of twosimultaneous phases (optimally separated by 90°) would be one preferredembodiment of the invention, as that would allow for almost completeremoval of autocorrelation noise and calculation of complex double-sidedspectra with the least complexity and expense.

The light source 72 in the aforementioned embodiments is preferably alow-coherence source. Multiple light sources 72 and 106, may also beused. The spectrometers 66 and 71 used in the FDOCT embodiments shouldpreferably be selected for maximum optical throughput and optimalmatching of their dispersion to the spectral content of thelow-coherence source, to avoid artifacts associated with the spatialfrequency response of the array (i.e., the dispersion should be chosenso that the spectrum nearly fills the detector array). Gratingspectrometers currently exhibit the optimal combination ofcharacteristics to satisfy these constraints, however other spectrometertypes may be used. If space utilization is not a serious constraint,prism-based spectrometers may give better throughput at the cost ofincreased required path length.

Preferably, the detector arrays utilized are photodiode arrays with themaximum well depth available, and optimized for response in thewavelength range of the source. Using current detector array technology,this corresponds to the use of silicon photodiode arrays for the popular830 nm OCT window and for any other desired OCT spectral windows belowapproximately 1000 nm, and for InGaAs photodiode arrays for the popular1310 nm OCT window and for any other desired OCT spectral windows in thenear-infrared beyond 1000 nm. Charge-coupled device (CCD) arrays mayalso be used, however current-generation CCDs utilize silicon substratesand may thus be unsuitable for imaging at the popular OCT wavelengthsabove 1000 nm.

For simplicity, FIGS. 1-7 above illustrate the phase-delayed spectralchannels as being dispersed and detected in separate detectors. As shownin FIG. 8, however, the spectrometers and arrays in the detectors shownin each implementation can be replaced by a single imaging spectrometerhaving a multiple-stripe or two-dimensional detector array, with theinput fibers arranged in close vertical proximity to one another so asto have their spectra imaged onto the separate rows (stripes) of thedetector array. Such an arrangement would have the significantadvantages of allowing for optimal matching of the spectra placed on allchannels (since all channels would use the same grating and otherspectrometer optics), as well as the cost and space savings achievableby using a single spectrometer. Dual-stripe photodiode arrays have beencommercially available in the past, and also three-row CCD arraysdesigned for 3-color line scanning are currently commercially available.Two of the three rows of a 3-color line scanner array could also be usedin place of a dual-row array.

For a preferred embodiment of two FDOCT channels separated by 90° or180°, a single dual-stripe photodiode array mounted onto an imagingspectrometer would be the preferred detector. Alternatively, atwo-dimensional CCD or photodiode array could be used to either a)simulate a dual-stripe array by using the binning capabilities of suchan array to collect dual simultaneous spectra, or b) collect more thantwo simultaneous spectra through an appropriate alternative binningalgorithm. However, two-dimensional CCDs still have significantwell-depth limitations, and large two-dimensional photodiode arrays arenot yet commercially available.

It should be noted that the term “optical circulator” is used herein tomean any type of device capable of directional coupling ofelectromagnetic radiation incident on port 1 to port 2, whilesimultaneously coupling electromagnetic radiation incident on port 2 toport 3 Also, as used herein, a “fiber coupler” is used to mean anydevice which receives an input signal of electromagnetic radiation anddivides that signal between two output ports. It should be noted that asused herein, a fiber coupler may have multiple ports wherein each portcan serve as an input port for a selected pair of output ports as wellas function as an output port for a selected input port. The fibercoupler splitting ratio for all embodiments is ideally 50/50, howeverthis splitting ratio may be modified to account for nonideal performanceof other components, for example to compensate for the insertion loss ofcirculators or other elements. “Polarization controller” is used hereinto mean any semiconductor or bulk optical device used to selectivelymanipulate the polarization of an input signal and output themanipulated signal. “Optical fiber” is used to mean any device or set ofdevices used to direct electromagnetic radiation along a prescribedpath. Thus, “optical fiber” can mean a signal strand of opticallytransparent material bounded by a region of contrasting index ofrefraction, as well as mirrors or lenses used to direct electromagneticradiation along a prescribed path.

As used herein, “phase modulator” means any semiconductor or bulk deviceused to modulate or otherwise alter the phase of an inputelectromagnetic signal and output the manipulated electromagneticsignal. “Reflector” is used herein to mean any device capable ofreflecting an electromagnetic signal. Thus, “reflector” can be used tomean a mirror, an abrupt transmission in an index of refraction as wellas a periodically spaced array structure such as a Bragg reflector.“Scanning optics” means any system configured to sweep anelectromagnetic signal across a chosen area.

“Detector” is used herein to mean any device capable of measuring energyin an electromagnetic signal as a function of wavelength. Additionally,“source” is used to mean any source of electromagnetic radiation, andpreferably means a low coherence source of electromagnetic radiation.

The foregoing embodiments and advantages are merely exemplary and arenot to be construed as limiting the present invention. The presentteaching can be readily applied to other types of apparatuses. Thedescription of the present invention is intended to be illustrative, andnot to limit the scope of the claims. Many alternatives, modifications,and variations will be apparent to those skilled in the art. In theclaims, means-plus-function clauses are intended to cover the structuresdescribed herein as performing the recited function and not onlystructural equivalents but also equivalent structures.

1. A method, comprising: simultaneously acquiring a first spectrum and asecond spectrum having a first predetermined phase differencetherebetween from a signal manipulator; determining a first differencespectrum between the first and second spectra; simultaneously acquiringa third and fourth spectra having a second predetermined phasedifference therebetween from a signal manipulator, wherein the first andsecond spectra are orthogonal to the third and fourth spectra,respectively; determining a second difference spectrum between the thirdand fourth spectra; generating a complex Fourier-domain dataset from thefirst and second difference spectra, wherein the first differencespectrum comprises the real part of the complex Fourier-domain datasetand the second difference spectrum comprises the imaginary part of thecomplex Fourier-domain dataset; generating an inverse Fourier transformfrom the complex Fourier-domain dataset; and generating an image of atleast a portion of a sample based on the results of said inverse Fouriertransform.
 2. The method of claim 1, wherein the phase differencebetween the first spectrum and the third spectrum and between the secondspectrum and the fourth spectrum is approximately 90 degrees.
 3. AnFDOCT method, comprising: simultaneously acquiring a first spectrum anda second spectrum having a first predetermined phase differencetherebetween from a signal manipulator; determining a first differencespectrum between the first and second spectra; simultaneously acquiringa third and fourth spectra having a second predetermined phasedifference therebetween from a signal manipulator, wherein the first andsecond spectra are orthogonal to the third and fourth spectra,respectively; determining a second difference spectrum between the thirdand fourth spectra; generating a complex Fourier-domain dataset from thefirst and second difference spectra, wherein the first differencespectrum comprises the real part of the complex Fourier-domain datasetand the second difference spectrum comprises the imaginary part of thecomplex Fourier-domain dataset; generating an inverse Fourier transformof the complex Fourier-domain dataset; and generating an image of atleast a portion of a sample based on results of said inverse Fouriertransform.
 4. An EDOCT method, comprising; generating a first, second,third and fourth spectra, wherein there is a first predetermined phaseshift between the first and second, spectra, a second predeterminedphase shift between the second and third spectra, and a thirdpredetermined phase shift between the third and fourth spectra, whereinthe first, second, third and fourth spectra are simultaneously acquired;determining a first difference spectrum between the first and thirdspectra; determining a second difference spectrum between the second andfourth spectra; generating a complex Fourier-domain dataset from thefirst and second difference spectra, wherein the first differencespectrum comprises the real part of the complex Fourier-domain datasetand the second difference spectrum comprises the imaginary part of thecomplex Fourier-domain dataset; generating an inverse Fourier transformof the complex Fourier-domain dataset; generating an image of at least aportion of a sample based on results of said inverse Fourier transform.5. The method of claim 4, wherein the first predetermined phase shift isapproximately 90 degrees, the second predetermined phase shift isapproximately 90 degrees, and the third predetermined phase shift isapproximately 90 degrees.
 6. The method of claim 1, wherein the firstand second predetermined phase differences substantially correspond to acomplementary phase difference.
 7. The method of claim 6, wherein saidthe complementaly phase difference is substantially 180 degrees.
 8. AFourier domain optical coherence tomography (FDOCT) method, comprising:simultaneously acquiring at least a first spectrum and a second spectrumhaving a predetermined phase difference therebetween from a signalmanipulator, wherein the first and second spectra are interferometricspectra based on a interference between a reference path and a samplepath, wherein the first spectrum is acquired based on an interferencebetween a reference and a sample path having a first path lengthdifference therebetween and the second spectrum is acquired based on aninterference between a reference and a sample path having a second pathlength difference that is different from the first difference; andgenerating an image based on the first and second sprectra.
 9. Themethod of claim 8, wherein the predetermined phase difference betweenthe first and second spectra is approximately 90 degrees.
 10. The methodof claim 9, further comprising: generating a complex Fourier-domaindataset based on the first and second spectra, wherein the firstspectrum comprises the real part of the complex Fourier-domain datasetthe second spectrum comprises the imaginary part of the complexFourier-domain dataset; generating an inverse Fourier transform of thecomplex Fourier-domain dataset; generating an image of at least aportion of a sample based on results of the inverse Fourier transform.11. The method of claim 8 wherein the first and second spectra aresimultaneously acquired using polarization encoding.
 12. The method ofclaim 10, wherein polarization encoding comprises: acquiring the firstspectrum into one polarization state of the interference signal;simultaneously acquiring the second spectrum into the orthogonalpolarization state of the interference signal; separating the encodedspectra by means of a polarizing beamsplitter; and simultaneouslyrecording the spectra on separate detectors.